Failsafe protection from induced rf current for mri rf coil assembly having transmit functionality

ABSTRACT

An electrically-controlled failsafe switch is included in an MRI transmit-and-receive RF coil assembly so as to protect it from induced RF currents in the event it is disconnected from an MRI system, but inadvertently left linked to strong MRI RF fields during imaging procedures using other RF coils.

FIELD

The subject matter below relates generally to failsafe protection frominduced radio frequency (RF) currents in magnetic resonance imaging(MRI) RF coil assembly components where the RF coil has RF transmittingfunctionality (e.g., a transmit/receive (T/R) RF coil assembly).

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 illustrates an exemplary embodiment of an MRI system includingfailsafe protection from induced RF currents in an RF T/R coil assembly;

FIG. 2 is a schematic block diagram of an exemplary embodiment of an MRIRF T/R coil assembly of a type that might be used in the embodiment ofFIG. 1;

FIG. 3 a depicts a schematic equivalent circuit of an RF T/R coilelement and its feeding circuit as typically found in prior artinstallations subject to induced currents from ambient RF magneticfields in the MRI system if left unconnected therein during activationof the MRI system RF transmitter;

FIG. 3 b depicts a schematic equivalent circuit for an RF T/R coilelement subjected to such unintended induced RF currents, but nowprotected therefrom by an exemplary embodiment of a failsafeelectrically-controlled switch;

FIG. 4 is a schematic diagram of an exemplary electrically-controlledswitch that can be used to provide failsafe protection from induced RFcurrents in an MRI RF T/R coil assembly;

FIG. 5 is a more detailed schematic diagram of an embodiment similar tothat shown in FIG. 4, but now including DC bias circuitry components;

FIG. 6 is a schematic circuit diagram of another exemplary embodiment ofan electrically-controlled switch that may be used to provide failsafeprotection from induced RF currents in an MRI RF T/R coil assembly; and

FIG. 7 a, FIG. 7 b and FIG. 8 depict alternate exemplary embodimentswherein a safety switch is located other than at the feed point of an RFT/R coil element.

DETAILED DESCRIPTION

If an MRI RF T/R coil assembly (i.e., or a transmit-only coil assemblythat has a local transmit function) is unplugged from connection to theMRI system (i.e., it is not currently being used), it may be mistakenlyleft in the MRI system gantry area where it is subject to intense MRI RFmagnetic fields during imaging processes. If it does not have transmitdecoupling means, large induced RF currents may be caused to flow withinvarious components of the RF coil assembly. Typical removable RFreceive-only coils already have built in protection (e.g., they are onlyactive in the presence of weak RF fields emanating from the object beingimaged).

However removable RF coils having transmit functionality (e.g., T/Rcoils) typically have not been equipped with suitable built-in automaticprotection which leaves the coil assembly undamaged after an encounterwith such induced RF current, makes the coil assembly safe for patientsand others to be in contact with it throughout the encounter, and leavesthe coil assembly ready for immediate continued use after the encounter(e.g., without the need to replace any component thereof such as afuse). Large induced RF currents may damage the RF transmit or T/R coilassembly and/or endanger a patient or other person who comes intocontact with the assembly since it may have a greatly raised surfacetemperature. For example, such large currents may excessively heat someof the components and may present a potential burn risk to any patientwho is being imaged (e.g., by the use of other RF transmit coils at thatmoment—such as a large built-in fixed MRI system RF coil).

To provide failsafe protection to a transmit-only or a T/R MRI RF coilfrom such induced RF currents, several exemplary embodiments describedbelow use a suitable variable impedance (e.g., anelectrically-controlled switch) and respectively corresponding methods.In the exemplary embodiments, such variable impedance exhibit animpedance that changes between different impedance values in response toan electrical control current automatically provided when the RF coil isoperatively connected to the MRI system. In such a “connected” state,the electrically-controlled impedance permits substantially unimpededpassage of MRI RF currents between the MRI system and a protected MRI RFT/R coil (i.e., in a connected-receive mode and in a connected-transmitmode). However, in a failsafe “unconnected” condition, a differentimpedance state of the variable impedance is configured to automaticallysubstantially impede the passage of damaging induced RF currents withinthe RF T/R coil assembly. In effect, the switch exhibits three modes:two “connected” MRI operational modes and one fail-safe “unconnected”MRI non-operational mode.

The exemplary MRI system embodiment shown in FIG. 1 includes a gantry 10(shown in schematic cross-section) and various related system components20 interfaced therewith. At least the gantry 10 is typically located ina shielded room. One exemplary MRI system geometry, depicted in FIG. 1,includes a substantially coaxial cylindrical arrangement of the staticfield B0 magnet 12, a G_(x), G_(y) and G_(z) gradient coil set 14 and abuilt-in fixed RF coil assembly 15. Along the horizontal axis of thiscylindrical array of elements is an imaging volume 18 shown assubstantially encompassing the head of a patient 9 supported by apatient table 11.

An MRI system controller 22 has input/output ports connected to display24, keyboard 26 and printer 28. As will be appreciated, the display 24may be of the touch-screen variety so that it provides control inputs aswell.

The MRI system controller 22 interfaces with MRI sequence controller 30which, in turn, controls the G_(x), G_(y) and G_(z) gradient coildrivers 32, as well as the RF transmitter 34 and the transmit/receiveswitch 36. The MRI sequence controller 30 includes suitable program codestructure 38 for implementing MRI sequences available in the repertoireof the MRI sequence controller 30.

The MRI system 20 includes an RF receiver 40 providing input to dataprocessor 42 so as to create processed image data to display 24. In theexemplary embodiment, the receiver 40 is shown connected topre-amplifier 63 associated with removable RF T/R coil assembly 16 viaan interconnect interface 16 a, 16 b. However those in the art willappreciate that the receiver 40 may alternatively be connected withother RF coils, perhaps via other controlled RF switching circuitry notshown in FIG. 1 (e.g., a connection from the MRI system RF coil 15 isschematically depicted in dotted line in FIG. 1).

The MRI data processor 42 may also be configured for access to programcode structure 44 and to memory 46 (e.g., for storing data derived fromprocessing in accordance with the exemplary embodiments and the programcode structure 44).

Also illustrated in FIG. 1 is a generalized depiction of an MRI systemprogram store 50 where stored program code structures are stored incomputer-readable storage media accessible to the various dataprocessing components of the MRI system. As those in the art willappreciate, the program store 50 may be segmented and directlyconnected, at least in part, to different ones of the system 20processing computers having most immediate need for such stored programcode structures in their normal operation (i.e., rather than beingcommonly stored and connected directly to the MRI system controller 22).

Indeed, as those in the art will appreciate, the FIG. 1 depiction is avery high level simplified diagram of a typical MRI system with somemodifications so as to practice exemplary embodiments to be describedhereinbelow. The system components can be divided into different logicalcollections of “boxes” and typically comprise numerous digital signalprocessors (DSP), microprocessors, special purpose processing circuits(e.g., for fast A/D conversions, fast Fourier transforming, arrayprocessing, etc.). Each of those processors is typically a clocked“state machine” wherein the physical data processing circuits progressfrom one physical state to another upon the occurrence of each clockcycle (or predetermined number of clock cycles).

Not only does the physical state of processing circuits (e.g., CPUs,registers, buffers, arithmetic units, etc.) progressively change fromone clock cycle to another during the course of operation, the physicalstate of associated data storage media (e.g., bit storage sites inmagnetic storage media) is transformed from one state to another duringoperation of such a system. For example, at the conclusion of an imagingprocess, an array of computer-readable accessible data value storagesites in physical storage media will be transformed from some priorstate (e.g., all uniform “zero” values or all “one” values) to a newstate, wherein the physical states at the physical sites of such anarray vary between minimum and maximum values to represent real worldphysical events and conditions (e.g., the physical structures within animaged volume space). As those in the art will appreciate, such arraysof stored data values represent and also constitute a physicalstructure—as does a particular structure of computer control programcodes which, when sequentially loaded into instruction registers andexecuted by one or more CPUs of the MRI system 20, cause a particularsequence of operational states to occur and be transitioned throughwithin the MRI system.

As depicted in the exemplary embodiment of FIG. 1, an RF coil assembly16 is configured so that it may be removed (e.g., in favor of otherremovable RF coil assemblies and/or the more permanently installed RFcoil assembly 15 for some imaging procedures—e.g., see coil switch 17which may route transmitted RF to the fixed coil assembly 15 or to theremovable coil assembly connector interface 16 b) and manuallydisconnected from the MRI system via the manual mated plug/socketassembly interface 16 a, 16 b. In addition, an electrically-controlledfailsafe safety switch 60 a, 60 b is included in the removable T/R RFcoil assembly 16 (e.g., one for each of plural RF coil elements, if suchare present).

In the exemplary embodiment of FIG. 1, the exemplary removable RF T/Rcoil assembly 16 may constitute, for example, a quadrature detection(QD) RF “head” coil comprising plural coil elements, each of which isconfigured to electromagnetically couple RF fields with an object beingimaged (e.g., the patient's head) in the MRI system gantry 10. As willbe understood, the failsafe protection provided by the exemplaryembodiments is not limited to quadrature coils but may be otherwiseutilized, e.g., by arrayed transmit and/or T/R coils.

A more detailed block diagram of an exemplary RF coil assembly 16 isdepicted at FIG. 2. As those in the art will appreciate, a typical QDhead coil will include two RF coil elements (e.g., 61 a, 61 b) which arespatially and electrically offset relative to one another by 90 degrees.Thus, FIG. 2 includes a schematic depiction of a 90 degree hybrid powercombiner/splitter to effect an electrical RF phase shift between the twoRF coil elements. As those in the art will appreciate, such hybrid powercombiner/splitter may be located in the T/R switch (as schematicallyshown in FIG. 2) or elsewhere before or after the T/R switch (e.g.,anywhere between the coil loop element and the power amplifier remotelylocated in the MRI system). As will also be appreciated, such phaseshifting is not always required in all multi-coil element MRI RF coilassemblies.

In the exemplary embodiment, a failsafe safety switch (e.g., 60 a, 60 b)is serially connected with each RF coil element. That is, there is aseparate serially connected safety switch respectively associated witheach RF coil element in this exemplary embodiment. However, as those inthe art will appreciate, other arrangements of a failsafe safety switchmay be found effective in certain RF coil assembly configurations (e.g.,the switch may be positioned at the feed point of an RF coil element,within the RF coil element or at some other suitable RFwavelength-related impedance-sensitive control position within the RFcircuitry).

The transmit/receive (T/R) switch 36 (which may be remotely located aspart of the MRI system) is controlled by sequence controller 22 toeffectively connect appropriate RF transmitter/amplifier circuits 34 ofthe MRI system or RF receive circuits 40 of the MRI system to thedifferent RF coil elements as appropriate for a particular dataacquisition sequence—and, of course, a particular MRI RF coil assemblystructure/configuration. Dedicated separate transmit and receive RFcoils may also be used—in which case a T/R switch may not be needed. Inthe exemplary embodiment of FIG. 2, suitable RF receivebuffer/preamplifier circuitry 63 is co-located within the RF coilassembly 16. Of course there may be plural receive amplifiers toaccommodate N plural receive channels—as is schematically depicted inFIG. 2. As also depicted in FIG. 2, the RF coil assembly 16 is suitablefor manual connection to the MRI system via plug connector interface 16a (and a mating socket 16 b associated with the MRI system).

In the exemplary embodiment of FIG. 2, the interface connection betweenthe RF coil elements and the T/R switch is made via lengths of coaxialcable transmission line 64, 65 (e.g., possibly of 60 cm or so inlength). Other interface connection circuitry may, of course, beemployed instead of a “cable”. Typically, such interface circuitry mayinclude a transmission line circuit having a characteristic impedance of50 ohms. In the exemplary embodiment of FIG. 2, the safety switches 60a, 60 b are preferably located and connected closely to the coil elementfeed points with interconnecting transmission line lengths 64, 65extending between the safety switches and the T/R switch 36. However, aswill be appreciated, other appropriate functional locations for thesafety switches may be employed.

As those in the art will appreciate, the MRI RF coil assembly 16typically will be functionally and aesthetically disposed within asuitable housing so as to accommodate a particular patient body part(e.g., a head in this exemplary instance).

Since the construction of the RF coil elements, T/R switch, transmitamplifiers, receive amplifiers, MRI system, etc., can be of conventionaldesign, no further details need be discussed for these elements.However, it should be noted that in the exemplary embodiment, if a DCbias circuit through relevant RF components does not already exist, itis now provided through connector 16 a, 16 b and various RF circuits asneeded to pass DC bias current from the MRI system to the safetyswitch(es)—e.g., by using suitable low-pass frequency filtering elements(e.g., inductors) for passing DC bias currents and/or high-pass DCblocking capacitors to define the DC bias circuit.

In the exemplary embodiment of FIG. 2, the failsafe safety switches 60a, 60 b include an electrically-controlled switch having at least onevariable impedance component connected to an appropriateimpedance-control point within or to the respectively corresponding RFcoil element. The variable impedance component is configured to changeits impedance to the passage of electrical currents between differentimpedance states in response to an electrical control signal (e.g., a DCbias control current) that is automatically provided from the MRI systemwhenever plug 16 a is connected thereto. The DC bias current path may beprovided in the RF circuitry comprising components 63, 34, 17, 36, 16 a,16 b, 63, 64 and 65 that also conduct DC bias control currents to thefailsafe safety switches 60 a, 60 b. In the failsafe mode (i.e., whenthe coil assembly 16 is not connected to the MRI system via plug 16 a),no DC bias control current is available and the safety switches 60 a, 60b then revert to an impedance state that effects substantial attenuationof induced RF currents to the coil elements if the coil assembly 16happens to have been mistakenly left within the gantry area such that itis subjected to intense RF magnetic fields when the MRI system isactivated (e.g., to image some different portion of the patient usingsome other RF coil assembly).

On the other hand, when the coil assembly 16 is connected to the MRIsystem via the manually actuated plug interlace connector 16 a, then aDC bias control current is supplied to the safety switches and thistransitions the variable impedance component to a different impedancestate that permits substantially unimpeded passage of MRI RF currents toand/or from the coil assembly 16 during imaging procedures using thecoil assembly 16.

In connection with the FIG. 2 exemplary embodiment, it will be seen thatRF coil element 61 a, safety switch 60 a and transmission line 64constitute an MRI RF coil device sub-assembly that is (indirectly inthis particular example) manually connected to an MRI system. The RFcoil element 61 a is configured to electromagnetically coupletransmitted and received RF fields to/from an object (e.g., a patient'shead) being imaged in an MRI system gantry. The electrically-controlledswitch 60 a has at least one variable impedance component connected toan appropriate impedance control point associated with RF coil element61 a, that variable impedance component being configured to change itsimpedance to the passage of electrical currents between a firstimpedance state and a second different impedance state in response to anelectrical control current or signal (e.g., DC bias current) providedwhen the RF coil device is connected to the MRI system.

In the exemplary embodiment, an MRI RF T/R coil device sub-assembly alsocan be considered as including the transmit/receive switch 36 which, inthis exemplary embodiment, is included as a part of a T/R coil assemblyand configured to pass both RF and DC bias control currents from/to RFtransmit/receive circuitry. As noted, such T/R switch may also be moreremotely located in the MRI system in some embodiments.

The exemplary device sub-assembly typically may include the RF receivepreamplifier circuit 63 as part thereof that is also manuallyconnectable to RF receiver circuitry 40 in the MRI system (via theconnection interface 16 a, 16 b). Typically the RF receive pre-amplifier63 will be located relatively close to the RF coil elements.

As will be appreciated, in this exemplary system at least one of thetransmit RF circuitry or the receive RF circuitry is configured to passDC bias control current emanating from the MRI system (and passedconcurrently with RF currents therealong through an auxiliary DC biascurrent path) and passing at least to the variable impedancecomponent(s).

As those in the art will appreciate, and as represented by a series ofdots leading to Nth elements in FIG. 2, there may be RF coil assemblieshaving a single RF in/out port, a pair of RF in/out ports, or more. Inparticular, some currently known RF coil assemblies utilize fourseparate RF in/out ports (e.g., for improved image uniformity,especially at higher static magnetic field levels).

FIG. 3 a depicts a schematic equivalent circuit for a typical prior artcircuit having an RF T/R coil element 80 that may be subjected tointense RF B1 magnetic field flux 81 linked to the coil element 80 ifthe coil is left unconnected within the MRI gantry during imagingprocedures using other coils. As depicted in FIG. 3 a, the feedingcircuit (including interface transmission path 64, T/R switch 36, RFreceive amp 63 and a suitable electrical interface circuit (e.g.,another RF transmission path) to and through connector 16 a shown inFIG. 2) can be considered as reduced to the equivalent LCR circuit shownin FIG. 3 a. Although the exact current values flowing in any giveninstallation may greatly vary, some simulated possible currentmagnitudes for induced currents are depicted in FIG. 3 a. For example,perhaps 3 amps may be passed to the RF feeding circuits (and beyond),while perhaps 4.7 amps may flow in the coil element 80 itself. Since thecoil element and capacitance are relatively low loss components, theymay not heat up so much. However, as will be appreciated, suchsignificant induced RF currents (especially over time) may substantiallyheat the more lossy (i.e., resistive) feeding circuit components and/orlinked remote circuits which can more effectively absorb ambient RFelectromagnetic energy. This may damage such components (perhaps soseverely as to require replacement) and/or may provide rather extremetemperatures, thus creating a safety hazard for technicians and/orpatients who may be in contact with or accidentally come into contactwith such a misplaced RF coil assembly. For example, surfacetemperatures may reach more than 41° C. (even before a fuse is blowneven if a fuse had been included in the prior art circuitry). Suchextreme temperatures may cause patients, technicians and others cominginto contact with such a misplaced coil assembly to be severely injured.

FIG. 3 b schematically depicts an equivalent circuit for an exemplaryembodiment wherein the resistive impedance of the feeding circuitry(including any linked remote circuitry) has been greatly increased(e.g., from 50 ohms to 1,000 ohms). In this embodiment, under similarassumed simulation conditions as for FIG. 3 a, it will be seen that thesimulated exemplary induced currents are significantly reduced (withinboth the feeding circuit and any linked remote circuitry). The exemplaryinduced current within the RF coil element may be reduced approximatelyto the level of normal use while within the feeding circuit the inducedcurrent is much more greatly reduced so as to produce very little, ifany, significant heating in the overall RF coil assembly.

A more detailed exemplary embodiment of an electrically-controlledswitch suitable for use in this application is depicted in the schematicdiagram of FIG. 4. In FIG. 4, the parallel LC circuit componentscomprising inductor L1-4 and capacitors C1-4 and C2-4 are dimensioned toprovide parallel resonance (i.e., maximum impedance) at the expected RFoperating frequency of the MRI system (e.g., approximately 63.86megahertz in a 1.5 Tesla MRI system and approximately 127.73 megahertzin a 3 Tesla system). The pair of back-to-back connected diodes D1-4 andD2-4 are connected across at least a portion of the parallel LC circuitand configured to present a lowered RF impedance if both are forwardlybiased (which detunes the LC circuit from resonance). The lowerednon-resonant impedance thus permits intended MRI RF imaging currents toflow substantially unimpeded to the coil element. However, when notforwardly biased (e.g., when the RF coil assembly is not connected tothe MRI system), the back-to-back connected diodes leave the LC circuitto present a substantial parallel resonance impedance that substantiallyobstructs the flow of induced RF currents in the event that theunconnected coil device nevertheless remains within an MRI systemlocation where it can be exposed to MRI system RF transmit fields (e.g.,from other RF coils that would otherwise induce dangerous RF currents inthe coil element/feeding circuit components).

For the exemplary embodiments, the following Table 1 demonstrates anexemplary relationship between the three operational states of the RFcoil assembly, the failsafe switch impedance state and the DC biascontrol voltage.

TABLE 1 Failsafe Switch DC Bias Control Operational State ImpedanceVoltage Unconnected: High (OFF) No voltage External RF exposureConnected: Low (ON) High (ON) Normal Tx RF Connected: Low (ON) High (ON)Normal Receive RF

The more detailed embodiment of FIG. 5 includes exemplary DC biascontrol current paths provided via the inductors L2-5, L3-5 andcapacitor C1-5. As will be appreciated, the capacitor C1-5 isdimensioned so as to present a substantial short-circuit at the intendedRF operating frequencies. In this embodiment, the parallel resonant LCcircuit comprises the inductance L1-5 and the serial connected capacitorC2-5, as well as the serially connected pairs (of parallel connected)capacitors C3-5, C4-5, C5-5, C6-5. The DC bias current source (e.g.,represented schematically by battery B) is located remotely as part ofthe MRI system and is thus shown with a dotted line connection in FIG.5.

In the FIG. 5 embodiment, the failsafe switch 100 is preferablyconnected to its associated RF coil element feed point via inductor L16(dimensioned suitably so as to provide impedance matching) andDC-blocking capacitors C96, C97. However, as will be described in moredetail below, other suitable impedance control points in the RF coilelement and/or its RF feed path may be chosen as the location for thefailsafe switch 100.

In the FIG. 5 embodiment, the pair of back-to-back connected PIN diodesis connected across only part of the capacitance in the parallelresonant LC circuit so as to reduce the voltage across the PINdiodes—and thus help control maximum diode temperatures during theunplugged failsafe condition. However, the ratio of the splitcapacitance in the resonant LC circuit may also change the effective RFlosses in the normal connected modes (which might be somewhatcounteracted by using a relatively higher inductance value in thecircuit if this can be achieved while still achieving desired impedancematching in the normal connected modes). Those in the art will recognizethat dimensioning of the circuit values in all of the exemplaryembodiments may well involve some design trade-offs and even trial anderror to discover an optimum set of circuit component dimensions for agiven particular RF coil assembly and the associated MRI system.

Another detailed embodiment is depicted schematically at FIG. 6 for afailsafe switch 102. Here, there is no parallel resonant LC circuitinvolved. Instead, there is simply a plurality of serially connectedback-to-back diodes D1-6, D2-6, D3-6, D4-6, D5-6, D6-6). A suitable DCbias control circuit is provided by inductors L1-6, L2-6, L3-6 andcapacitors C1-6, C2-6 (e.g., to conduct DC bias current from a source inthe MRI system schematically represented in FIG. 6 as battery Bconnected in dotted line between an RF coaxial cable center conductorand system ground). If left un-connected to the MRI system (e.g., viathe T/R switch and other RF circuitry if included as part of the RF coilassembly), these plural back-to-back unbiased diodes present asubstantial impedance that substantially obstructs the flow of inducedcurrents. However, if the switch 102 is connected to the MRI system,then DC bias control currents forwardly bias all of the diodes such thata lowered RF impedance is presented, thus permitting MRI RF imagingcurrents to flow substantially unimpeded to/from the respectivelyassociated coil elements. Once again, an impedance matching inductanceL17 is provided in the feed to the coil elements and, in this exemplaryembodiment as well, DC blocking capacitances C98, C99 are employed.

Also present in the exemplary embodiment of FIG. 6 is a resistanceconnected in parallel across each diode. The resistances R1, R2, R3, R4,R5, R6 are of substantially equal resistance values (e.g., 4.4K ohms) soas to establish substantially equal RF induced voltage drops across thediodes having the same orientation of polarity during the time they aresimultaneously reverse-biased by induced RF current (i.e., whensubjected to induced RF current and the forward bias control current isnot present).

In the FIG. 6 embodiment, the use of more than one pair of back-to-backconnected diodes helps distribute heat that is generated from theinduced RF current flow.

In the exemplary embodiments, the diodes may be PIN diodes havingrelatively high reverse voltage breakdown characteristics (e.g., greaterthan 500 volts) and relatively small forward resistance. Typically, abias current of approximately 150 milliamperes may suffice.

The exemplary embodiments can cause the effective quality factor (i.e.,Q-factor) of the equivalent circuit (in its unconnected state) to beenhanced (e.g., possibly by 20-fold) so as to help ensure relativelysmall amounts of heat generation in the RF coil element itself. Ifpossible, the effective high resistance state of the switch (e.g., whenunconnected to the MRI system) should be approximately 1 kilohm orgreater.

Some exemplary currently available suitable PIN diodes may be obtainedfrom Macom Technology as diode part number MA4P7470E-1072T (having areverse breakdown voltage of 800 volts) or MA4P7446F-1091 (having areverse breakdown voltage of 600 volts). Whatever variable impedanceelement is used, the reverse breakdown voltage should be relatively high(e.g., preferably at least 500 volts if used in the context of a QD headcoil).

The embodiment of FIG. 5 has an equivalent low impedance resistance ofabout 5 ohms with typical component choices—while the embodiment of FIG.6 for similar component choices may exhibit an equivalent low resistanceof about 1.8 ohms. Under some circumstances, it may be preferable to usethe lower resistance embodiment—although proper design of eitherexemplary embodiment may achieve acceptable, perhaps almost equal,results.

Preferably, the electrically-controlled switch in the exemplaryembodiments will effectively isolate the passage of the induced RFcurrent link relatively close to the RF coil feeding points. That is,the exemplary electrically-controlled switches preferably may be locatedas close as feasible to the RF coil element feed points. As a result,relatively small amounts of induced RF energy will be transferred to theT/R switch and other more remote (i.e., more proximate the MRI system)RF circuitry components. At the same time, the heat generated by inducedRF currents at the feed points is reduced as well.

Although exemplary embodiments have been described with the safetyswitches preferably located at coil feeding points, a safety switch canalternatively be located in series in one or more of RF coil elementloops as shown in FIG. 7 a (single loop-type) and FIG. 7 b(birdcage-type), or can be located at an electrically equivalentimpedance-control position such as one-half wavelength (or an integermultiple thereof) away from the feed point as depicted in FIG. 8. Ofcourse another suitable impedance point for a safety switch might be atone-quarter wavelength (or an odd integer multiple thereof) away fromthe feed point (in which case the variable impedance high-impedance andlow-impedance states would be reversed for achieving comparable coilmodes as compared to when the safety switch is located at one or morehalf-wavelengths from the feed point).

While certain embodiments of the inventions have been described, theseembodiments have been presented by way of example only, and are notintended to limit the scope of the inventions. Indeed, the novel methodsand systems described herein may be embodied in a variety of otherforms; furthermore, various omissions, substitutions and changes in theform of the methods and systems described herein may be made withoutdeparting from the spirit of the inventions. The accompanying claims andtheir equivalents are intended to cover such forms or modifications aswould fall within the scope and spirit of the inventions.

1. An MRI RF coil assembly having RF transmit functionality and which ismanually connectable to an MRI system, said RF coil assembly comprising:an MRI RF coil configured to electromagnetically transmit MRI RF fieldsto an object being imaged in an MRI system gantry when MRI RF current ispassed through said coil; RF feed circuitry configured to feed MRI RFcurrent to said coil from a manually operated connection interface withan MRI system; and at least one variable impedance electricallyconnected within or to at least one of said RF coil and said feedcircuitry, said variable impedance being configured to change itsimpedance to passage of RF current between different first and secondimpedance states in response to said RF coil assembly being disconnectedfrom said MRI system, said at least one variable impedance therebyautomatically protecting the coil assembly from excessive induced RFcurrent flow when the coil assembly is not connected to the MRI system.2. An MRI RF coil assembly as in claim 1, wherein said at least onevariable impedance is connected serially within an RF coil element. 3.An MRI RF coil assembly as in claim 1, wherein said at least onevariable impedance is connected serially at a feed point of an RF coilelement.
 4. An MRI RF coil assembly as in claim 1, wherein said at leastone variable impedance is connected to said RF feed circuitry between afeed point of an RF coil element and said connection interface.
 5. AnMRI RF coil assembly as in claim 1 further comprising: atransmit/receive switch disposed as part of said RF feed circuitrybetween said connection interface and an RF coil element; and RF receiveamplifier circuitry connected between said transmit/receive switch andsaid connection interface thereby providing a transmit/receive MRI RFcoil assembly.
 6. An MRI RF coil assembly as in claim 5 constituting abirdcage coil assembly comprising a plurality of said RF coils, eachwith its own respectively associated (a) RF feed circuitry, and (b) atleast one variable impedance which automatically changes betweendifferent impedance values when the coil assembly is disconnected froman MRI system.
 7. An MRI RF coil assembly as in claim 1, wherein said atleast one variable impedance comprises an electrically-controlled switchhaving at least two back-to-back serially connected diodes.
 8. An MRI RFcoil assembly as in claim 1, comprising an array of said RF coils,variable impedances and RF feed circuitry.
 9. An MRI RF coil assembly asin claim 1, wherein said at least one variable impedance comprises anelectrically controlled switch and said RF feed circuitry includes a DCbias current path extending from said connection interface with said MRIsystem to at least said electrically-controlled switch.
 10. An MRI RFcoil assembly as in claim 1, wherein said variable impedance comprises:a parallel LC circuit resonant at an RF operating frequency of said MRIsystem; at least one pair of back-to-back connected diodes connectedacross at least a portion of said parallel LC circuit and configured to:(a) present a lowered RF impedance which detunes said LC circuit fromresonance in the presence of a bias control current forward biasing saiddiodes, thus permitting MR RF imaging currents to flow substantiallyunimpeded to an RF coil element, and (b) otherwise, when not forwardbiased, leaving said LC circuit to present a substantial parallelresonant impedance which substantially obstructs the flow of induced RFcurrents in the event that said RF coil assembly is not electricallyconnected to said MRI system, but the RF coil assembly neverthelessremains in an MRI system location where the RF coil assembly can beexposed to MRI system RF transmit fields which induce RF current in saidRF coil assembly.
 11. An MRI RF coil assembly as in claim 1, whereinsaid variable impedance comprises: a plurality of serially connectedback-to-back diodes configured to: (a) present a lowered RF impedance inthe presence of a bias control current forward biasing said diodes, thuspermitting MR RF imaging currents to flow substantially unimpeded to anRF coil element, and (b) otherwise, when not forward biased, present asubstantial impedance which substantially obstructs the flow of inducedRF currents in the event that said coil assembly is not electricallyconnected to said MRI system, but the RF coil assembly neverthelessremains in an MRI system location where the RF coil assembly can beexposed to MRI system RF transmit fields which induce RF current in saidRF coil assembly.
 12. An MRI RF coil assembly as in claim 11, furthercomprising: a resistance connected in parallel across each said diode,said resistances being of substantially equal resistance values so as toestablish substantially equal voltage drops across said diodes whenreverse biased by induced RF current.
 13. An MRI system comprising saidMRI RF coil assembly as in claim
 1. 14. An MRI RF coil assembly havingRF transmit functionality and which is manually connectable to an MRIsystem, said RF coil assembly comprising: MRI RF coil circuitryconfigured to electromagnetically transmit RF fields to an object beingimaged in an MRI system gantry; and means connected to said RF coilcircuitry for automatically substantially impeding the flow of inducedRF current within said coil assembly when the coil assembly is notconnected to an MRI system.
 15. An MRI RF coil assembly as in claim 14,wherein said RF coil circuitry comprises: a transmit/receive switchconnected to RF receive amplifier circuitry, to said RF coil and to amanually operated connection interface with an MRI system, saidtransmit/receive switch and said RF receive amplifier circuitryincluding a DC bias current circuit configured to pass DC bias controlcurrent from a connected MRI system to said means for automaticallysubstantially impeding the flow of induced RF current.
 16. An MRI RFcoil assembly as in claim 14, wherein said means for automaticallyimpeding the flow of induced RF current is serially connected between anRF coil and an electrical interface to an MRI system.
 17. An MRI RF coilassembly as in claim 16, wherein said means for automatically impedingthe flow of induced RF current is connected at a feed point of said RFcoil.
 18. An MRI RF coil assembly as in claim 14, wherein said means forautomatically impeding the flow of induced RF current is seriallyconnected within an RF coil.
 19. A method of protecting a manuallyconnectable MRI RF coil assembly having transmit functionality frominduced RF currents in the event the coil assembly is unconnected froman MRI system, but left in a position electromagnetically linked to RFfields of an operating MRI system, said method comprising: disposing avariable impedance element serially with each RF coil in such assemblyand a manually operated electrical interface to an MRI system when thecoil assembly is in use; and automatically changing the impedance ofsaid variable impedance element when the coil assembly is disconnectedfrom an MRI system to automatically protect the coil assembly fromexcessive induced RF current flow when the coil assembly is notconnected to an MRI system.
 20. A method as in claim 19, wherein saidautomatically changing step comprises removing a DC bias current fromsaid variable impedance element otherwise passing thereto through saidelectrical interface.